US8193821B2 - Sensor system and methods for the capacitive measurement of electromagnetic signals having a biological origin - Google Patents
Sensor system and methods for the capacitive measurement of electromagnetic signals having a biological origin Download PDFInfo
- Publication number
- US8193821B2 US8193821B2 US11/722,495 US72249505A US8193821B2 US 8193821 B2 US8193821 B2 US 8193821B2 US 72249505 A US72249505 A US 72249505A US 8193821 B2 US8193821 B2 US 8193821B2
- Authority
- US
- United States
- Prior art keywords
- electrode
- signal
- sensor system
- signal processing
- electrode device
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active, expires
Links
- 238000005259 measurement Methods 0.000 title claims abstract description 108
- 238000000034 method Methods 0.000 title claims abstract description 74
- 238000012545 processing Methods 0.000 claims abstract description 80
- 238000012360 testing method Methods 0.000 claims abstract description 8
- 230000002452 interceptive effect Effects 0.000 claims abstract description 4
- 230000008859 change Effects 0.000 claims description 20
- 230000003068 static effect Effects 0.000 claims description 17
- 230000002123 temporal effect Effects 0.000 claims description 14
- 230000003071 parasitic effect Effects 0.000 claims description 13
- 238000013461 design Methods 0.000 claims description 11
- 239000012212 insulator Substances 0.000 claims description 11
- 230000008878 coupling Effects 0.000 claims description 10
- 238000010168 coupling process Methods 0.000 claims description 10
- 238000005859 coupling reaction Methods 0.000 claims description 10
- 230000001939 inductive effect Effects 0.000 claims description 7
- 239000000463 material Substances 0.000 claims description 5
- 230000005540 biological transmission Effects 0.000 claims description 4
- 230000008569 process Effects 0.000 claims description 4
- 230000007613 environmental effect Effects 0.000 claims description 3
- 239000007787 solid Substances 0.000 claims description 3
- 238000010292 electrical insulation Methods 0.000 claims description 2
- 239000000615 nonconductor Substances 0.000 claims description 2
- 230000005672 electromagnetic field Effects 0.000 abstract description 6
- 230000004044 response Effects 0.000 description 15
- 239000003990 capacitor Substances 0.000 description 11
- 230000006870 function Effects 0.000 description 7
- 230000000694 effects Effects 0.000 description 5
- 230000008901 benefit Effects 0.000 description 4
- 230000000875 corresponding effect Effects 0.000 description 4
- 238000010586 diagram Methods 0.000 description 4
- 230000002596 correlated effect Effects 0.000 description 3
- 210000003128 head Anatomy 0.000 description 3
- 230000003287 optical effect Effects 0.000 description 3
- 238000004458 analytical method Methods 0.000 description 2
- 238000004364 calculation method Methods 0.000 description 2
- 238000000354 decomposition reaction Methods 0.000 description 2
- 230000009977 dual effect Effects 0.000 description 2
- 239000013307 optical fiber Substances 0.000 description 2
- 238000001228 spectrum Methods 0.000 description 2
- 230000001629 suppression Effects 0.000 description 2
- 230000036962 time dependent Effects 0.000 description 2
- 238000012546 transfer Methods 0.000 description 2
- 230000006978 adaptation Effects 0.000 description 1
- 230000003044 adaptive effect Effects 0.000 description 1
- 238000013528 artificial neural network Methods 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 230000007177 brain activity Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 238000003066 decision tree Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 230000005684 electric field Effects 0.000 description 1
- 229940124645 emergency medicine Drugs 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000000605 extraction Methods 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 229920002457 flexible plastic Polymers 0.000 description 1
- 239000000499 gel Substances 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 238000012880 independent component analysis Methods 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 230000003340 mental effect Effects 0.000 description 1
- 238000005312 nonlinear dynamic Methods 0.000 description 1
- 230000005693 optoelectronics Effects 0.000 description 1
- 230000035790 physiological processes and functions Effects 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 238000012805 post-processing Methods 0.000 description 1
- 238000003672 processing method Methods 0.000 description 1
- 230000009467 reduction Effects 0.000 description 1
- 210000004761 scalp Anatomy 0.000 description 1
- 238000012706 support-vector machine Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/18—Shielding or protection of sensors from environmental influences, e.g. protection from mechanical damage
- A61B2562/182—Electrical shielding, e.g. using a Faraday cage
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
- A61B5/282—Holders for multiple electrodes
Definitions
- the invention relates to a sensor system for the capacitive measurement of electromagnetic signals having a biobiological origin in accordance with the preamble of claim 1 .
- the invention further relates to two methods for the capacitive measurement of electromagnetic signals having a biobiological origin, in particular by using the inventive sensor system.
- Such a sensor system for the capacitive measurement of electromagnetic signals having a biobiological origin comprises a capacitive electrode device, an electrode shielding element, at least partially surrounding the electrode device, for shielding the electrode device against external electromagnetic interference fields and a signal processing device for processing electromagnetic signals that can be detected by means of the electrode device.
- Such sensor systems are normally used in medical technology, in particular in order to record signals having a biobiological origin for electroencephalograms (EEGs) and electrocardiograms (ECGs).
- the capacitive measurement of the electromagnetic signals having a biobiological origin exhibits a range of advantages over the methods, known from the prior art, of using electrode devices galvanically coupled to a measurement object. Particularly in the case of the recording of an EEG, the frequently tiresome preparatory work of clearing hair from the measurement areas on the head of a test subject, and of reducing the electrical resistance of the scalp in these areas, for example by using a peeling agent in addition to the electrode gels required in any case, is eliminated. In the case of a capacitive coupling between a measurement area of the test subject and an electrode device, the electrical resistance of the coupling region is no longer relevant.
- Capacitive sensor systems of the generic type are respectively disclosed in US 2003/0036691 A1 and WO 03/048789 A2.
- the capacitive sensor systems known from the prior art and intended for measuring electromagnetic signals having a biobiological origin react sensitively to external electromagnetic interference fields despite the electrode shielding element that is present.
- additional shielding means for shielding out external electromagnetic interference fields at least partially surround the electrode device and the electrode shielding element in three dimensions.
- the additional shielding means are designed in this case with different compartments, the signal processing device being arranged in one such compartment.
- additional shielding means is to be understood within the scope of the present invention such that apart from the electrode shielding element additional shielding means are provided that are arranged separately therefrom in three dimensions. However, being separated in three dimensions is not to be interpreted to the effect that the additional shielding means are arranged without making mechanical and/or electrical contact with the electrode shielding element. Thus, it is by all means possible to provide an electrical contact between the shielding means and the electrode shielding element, for example for the purpose of ensuring an identical potential.
- the additional shielding means preferably surround the signal processing device at least partially.
- the additional shielding means can be designed both in such a way that the signal processing device is arranged in the region between the additional shielding means and the electrode shielding element, and in such a way that the additional shielding means at least partially surround both the electrode shielding element and the signal processing device.
- the shielding means therefore shields the signal processing device from the signal source and from the electrode device in such a way that no parasitic galvanic, capacitive or inductive influences react on the source or on the electrode device.
- a compact sensor system is provided in this way that is optimized with regard to shielding against external electromagnetic fields.
- the sensor system can be designed to be particularly compact by arranging the signal processing device adjacent to, that is to say in a fashion neighboring the electrode shielding element.
- the spatial proximity between the electrode device and signal processing device is attended by a range of advantages that is explained in yet more detail below.
- a signal processing device is regarded as any system that varies the incoming measurement signals, that is to say the system interacts with the measurement signals in such a way that the measurement signals have been varied upon passing through the system.
- a preferred variant of the sensor system provides that the additional shielding means at least partially surround the signal processing device in such a way that the additional shielding means shield the electrode device against electromagnetic interference fields originating from the signal processing device.
- the additional shielding means prefferably be designed in such a way that the electrode device and the signal processing device are covered so as to define a solid angle range from which originating electromagnetic signals can be detected by means of the sensor system, without being substantially influenced by the shielding means and/or the electrode shielding element.
- a further variant of the sensor system provides that the distance between the electrode shielding element and the electrode device and/or the geometry of the electrode shielding element and the electrode device and/or the dielectric properties of a filling in material arranged between the electrode shielding element and the electrode device are selected in such a way that the shielding capacitance between the electrode device and the electrode shielding element that results therefrom is small enough to minimize the coupling of noise signals of the signal processing device into the electrode device. It is ensured in this way that the signal path starting from the electrode device in the direction of the signal processing device functions essentially as a “one way street”.
- the electrode device which comprises at least one electrode element, is decoupled as far as possible in this way from the coupling of interference signals.
- the electrode capacitance of the electrode device forms a highpass filter with a cut-off frequency adapted to an electromagnetic signal, having a biobiological origin, to be measured relative to a measurement object. This measure also contributes to the aforementioned decoupling of the electrode device from the signal processing device.
- the geometry of the electrode device it is preferred for this to be selected in such a way that input noise signals of the parasitic impedance of the signal processing device lie with their upper cut-off frequency below the lower cut-off frequency for the signals to be measured.
- the sensor system includes a housing.
- This housing encloses the additional shielding means.
- the shielding means are designed as a component or components of the housing.
- the components can be designed in relation to the housing both as being of one piece and in a modular fashion.
- the electrode device is preferably coupled to the housing in such a way that the ohmic resistance between the electrode device and the housing is so high that a signal recorded capacitively by the electrode device is present at the input of the signal processing device without corruption.
- the capacitive electrode device is advantageously arranged in the housing in such a way that there can be no occurrence of any connections to electrical sources that entail the risk of disruption of the electrode device or the signal processing device.
- the sensor system includes, in particular, an electrical insulator region for the electrical insulation of the electrode device from a signal source. Said region is advantageously designed in such a way that both the electrode shielding element and the shielding means are galvanically isolated from a signal source during measurement of said signal source.
- the insulator region has material properties such that static charging of the insulator region by static environmental charges is minimized.
- the signal processing device of the sensor system preferably includes an impedance converter as input stage.
- the signal processing device has a difference amplifier.
- Particularly suitable in this case as difference signal is the signal of an external reference electrode that is in contact with the signal source.
- a particularly preferred variant of the sensor system is distinguished by an integrated analog-to-digital conversion of the signals.
- the signal processing device comprises an analog-to-digital converter and a digital signal processor.
- Such processors are available at a satisfactory level of miniaturization such that an appropriately compact sensor system can also be provided with this functionality.
- the input impedance of the signal processing device is advantageously to be selected in such a way that, together with the electrode capacitance of the electrode system, a highpass filter with a cut-off frequency adapted to an electromagnetic, having a biological origin, to be measured is formed.
- the electrode capacitance of the electrode system can, in particular, be set via the geometric parameters of the sensor system that have previously been explained.
- a highpass filter is preferably provided in the signal processing device in such a way that a signal amplified in the signal processing device passes through the highpass filter such that DC voltage potentials are isolated from the dynamic measurement signal.
- a further variant of the sensor system provides that the electrode device has a plurality of electrode elements for detecting electromagnetic signals having a biobiological origin.
- the plurality of the electrode elements acts in this case as a plurality of capacitive electrodes.
- a corresponding signal processing path is designed in the signal processing device for each of these electrode elements. It is also conceivable to provide a corresponding plurality of component signal processing devices.
- the sensor system preferably has an electrical line device shielded to ground potential, for routing the measurement signal away from the sensor system.
- Further variants of the sensor system have means for line-conductive transmission and/or means for lineless transmission of the measurement device signals from the sensor system to a receiving spaced apart therefrom. Signals can be transmitted optically and/or electrically both for the line-conductive and for the lineless variants.
- the sensor system has an optoelectronic transducer that is preferably of miniaturized design. Data can be transmitted both in free beam fashion and via optical waveguides such as optical fibers made from glasses or plastics.
- This reference electrode can be arranged next to the sensor system on a measurement object in such a way that the reference electrode provides a reference potential for the sensor system.
- the reference electrode is preferably designed in this case as an ohmic electrode.
- the reference electrode is coupled to the measurement object in a resistive, conductive or capacitive fashion.
- the reference electrode can also be used for coupling in an alternating signal by means of which a movement signal can be derived and it is therefore possible to compensate movement artefacts in the electromagnetic signal having a biobiological origin.
- the reference electrode fulfils a dual function, firstly that of providing the reference potential and secondly as a source for an alternating signal from which the movement signal can be derived and it is thereby possible to compensate movement artefacts.
- One or more reference electrodes can be used to feed in an alternating signal. When use is made of a number of reference electrodes, it is then possible to couple in alternating signals of different frequency, it being possible to separately compensate the movement artefacts of different electrode elements or electrode devices by means of each individual alternating signal.
- the sensor system described above can be integrated in a multiplicity of measuring devices.
- two that are suitable for recording EEGs and ECGs, in particular, are to be represented below.
- One measuring device comprises a multiplicity of sensor systems that are arranged in a helmet-like or cap-like carrier device.
- This carrier device is designed in such a way that it can be slipped at least partially over the head of a test subject.
- it preferably has wearing properties for the test subject that preclude the measurements from becoming unpleasant over lengthy time intervals. That is to say, the weight, the uptake of, or the transmissive properties for, body moisture etc. should be optimized for wearing comfort with the aid of appropriate materials.
- a measuring device in the form of a previously explained cap is of great use, particularly for EEG diagnostics in emergency medicine.
- a person wearing such a cap interacts via his/her brain activity with systems to be controlled. These systems to be controlled can be computers, artificial limbs, robots or further machines or complex systems to be monitored or to be controlled by a human being. In this case, the cap would serve as interface between man and machine.
- a second measuring device comprises a multiplicity of sensor systems, the sensor systems being arranged on a flexible carrier device of two-dimensional design that can be fastened on the body of a test subject.
- This measuring device is therefore suitable, in particular, for recording ECGs. The statements previously made apply correspondingly with regard to wearing comfort.
- the electrode devices and/or the housing and/or the additional shielding means and/or the electrode shielding elements are preferably produced from suitable flexible plastic in order to ensure that the measuring devices described previously have a flexibility adapted to the individual shape of head and body.
- a further aspect of the present invention consists in that in the case of a capacitive measurement of electromagnetic signals having a biobiological origin, the problem arises that even very slight relative movements between the capacitive sensor system and a signal source lead to clear inference signals.
- periodically occurring mechanical pulse wave caused by the movement of the heart of an organism is already sufficient to influence the measurement signal.
- a sensor system described above or of a measuring device described above When use is made of a sensor system described above or of a measuring device described above, it is provided to arrange the sensor system or the measuring device at a measurement object. Thereafter, an electrical alternating signal is coupled into the measurement object in order to use the temporal change in the alternating signal detected via the electrode device to determine the electrode capacitance of the electrode device of the sensor system, or the electrode capacitance of the electrode devices of the measuring device. This determined electrode capacitance is taken into account in a concluding step when evaluating the measurement signals of the sensor system or of the measuring device.
- the alternating signal coupled in can also be coupled out via a device other than the sensor systems used, and can be evaluated in order to determine electrode capacitance.
- the coupling in is performed, for example, via a separate electrode, arranged on the measurement object for this purpose.
- This electrode can be designed both as an ohmic and as a capacitive electrode.
- the frequency of the alternating signal coupled in is usually removed by more than one order of magnitude from the frequencies of the physiologically relevant measurement signals. It is possible in a way that is technically known to undertake to couple the alternating signal out by means of a lock-in amplifier circuit.
- the electrical alternating signal for determining the electrode capacitance of the electrode device of the sensor system or for determining the electrode capacitance of the electrode devices of the measuring device is preferably coupled into the measurement object via the electrode device or via a reference electrode cooperating externally with the sensor system or the measuring device.
- the reference electrode fulfils a dual function in this case.
- a capacitive sensor system suitable for measuring electromagnetic signals having a biobiological origin is arranged on a measurement object.
- An electrical alternating signal is then coupled into the measurement object, the alternating signal coupled in is then evaluated in order to determine the electrode capacitance of the sensor system, and then the electrode capacitance determined is finally taken into account when evaluating the measurement signals.
- One of the previously named methods can preferably be carried out in such a way that a line-frequency interference signal is used as electrical alternating signal.
- the 50 or 60 Hz signal of the power supply is present in any case and would not firstly need to be generated by means of a device provided specifically therefor.
- the movement thus determined can then be used to determine the movement artefacts superposed on the electromagnetic signals having a biological origin, and to compensate them.
- a further method making use of a previously described sensor system and/or of a previously described measuring device provides the following steps. Firstly, the sensor system or the measuring device is arranged on a measurement object. Subsequently, the position parameters of the position of the sensor system or of the sensor systems are determined relative to the measurement object during the measurement, and the determined position parameters are taken into account for the purpose of compensating movement artefacts in the measurement signal.
- All the sensor systems are provided with position measuring systems in order to determine the required position parameters. These position measuring systems determine the required relative position via a suitable measurement method. Suitable, in particular, to this end are optical, acoustic and piezoelectric devices and methods using these devices.
- the data are filtered, both spatially and in the frequency domain.
- all the filters can also be adapted to the instantaneous signal characteristic during the measurement, if appropriate in real time.
- use is made, in particular, of univariate denoising methods that are based on the decomposition of the signals into arbitrary—including overdetermined or underdetermined—base systems such as, for example, wavelets, sinusoidal functions etc.
- Univariate denoising means that a measurement signal of the sensor system per se is denoised in a fashion isolated from the other, parallel measurement signals of the sensor system.
- a number of measurement signals of the sensor system are denoised in a common process. These processes are based on a spatial projection of the measured data, for example with the aid of main component analysis, independent component analysis, projection pursuit techniques, sparse decomposition techniques or Bayesian subspace regularization techniques.
- projection techniques that take account of the geometry of the sensor system, in particular of the electrode device and of the shielding means and/or of the electrode shielding element such as, for example, beam-forming techniques, and laplace filters.
- Nonstationarities are understood very generally as changes in the environmental conditions, for example, the addition or omission of noise sources, relative movements between sensor system and measurement object, variation in the physiological state of the measurement object etc.
- the calibration data are also used in order to carry out a model selection (determination of the best suited method and of the values of the settable parameters).
- Such techniques for classification and regression can be used, for example, to distinguish different (brain) states on the basis of the measured and preprocessed measurement signals, and thus to transmit information. It is also possible to predict states.
- FIG. 1 a shows a schematic cross section of a first exemplary embodiment of the sensor system according to the invention
- FIG. 1 b shows a schematic cross section of a second embodiment of the sensor system according to the invention
- FIG. 2 shows a schematic equivalent circuit diagram of the sensor system according to the invention
- FIGS. 3 a - 3 c show three variants relating to the multipartite configuration of the electrode device of the sensor system
- FIG. 4 shows a schematic equivalent circuit diagram of an embodiment of a compensation circuit for compensating static charges on the electrode device
- FIG. 5 shows a schematic of the arrangement of the electrode device at a distance from the measurement object
- FIG. 6 shows a graph of the frequency spectrum of an alternating signal modulated by a movement of the electrode device
- FIG. 7 shows a graph of an alternating signal modulated by a movement of the electrode device, and of the movement signal calculated from the modulated alternating signal;
- FIG. 8 shows a flowchart of a method relating to the method for minimizing the influence of movement artefacts by using a sensor system
- FIG. 9 shows a flowchart of a second method relating to the method for minimizing the influence of movement artefacts by using a sensor system.
- FIG. 1 a shows a cross sectional illustration of a first embodiment of the sensor system according to the invention. This illustration is purely schematic and not true to scale.
- the electrode device 10 is arranged on an insulator element 12 of a dimensional design that acts as an insulator region.
- the electrode device 10 is surrounded essentially completely by an electrode shielding element 20 on the side of the insulator element 12 facing the electrode device 10 .
- This electrode shielding element 20 is likewise fitted on the insulator element 12 and galvanically decoupled from the electrode device 10 by the insulator element 12 .
- the electrode shielding element 20 has an opening for leading through a signal line 4 emerging from the electrode device 10 .
- This signal line 4 leads to a signal processing device 30 arranged outside the electrode shielding element 20 .
- Both the signal processing device 30 and the electrode shielding element 20 are surrounded by additional shielding means 21 on the side of the insulator element 12 facing the electrode device 10 .
- the additional shielding means 21 have a leadthrough for an electrical line device 40 , screened to frame potential, for routing the measurement signal away from the sensor system.
- the line device 40 shown can also be designed optically in the form of a light guide.
- the signal processing device 30 includes a suitable electrooptic transducer.
- the light guide could then be designed both as an optical fiber and in optically integrated fashion.
- the use of a light guide as line device 40 would have the advantage that said light guide would require no shielding against external electromagnetic fields.
- the insulator element 12 ensures, firstly, a galvanic decoupling of the electrode device 10 . Secondly, it likewise serves the purpose of galvanic decoupling between the electrode shielding element 20 and the additional shielding means 21 .
- the electrode shielding element 20 is designed in cross section as two L-shaped limbs arranged lying opposite one another. Of course, a multiplicity of other geometric configurations for example with cambered sections of the electrode shielding element 20 , are possible. It is especially important that the electrode shielding element 20 surrounds the electrode device 10 in such a way as to define a solid angle coming from which electromagnetic fields reach the electrode device 10 without experiencing attenuation caused by the electrode shielding element 20 in so doing.
- the additional shielding means 21 are valid mutatis mutandis with regard to the spatial configuration of the additional shielding means 21 .
- FIG. 1 b it is possible to design the additional shielding means 21 with different compartments. In one such compartment, it is then possible to arrange the signal processing device 30 in such a way that the additional shielding means 21 also shield the electrode device 10 together with the electrode shielding element 20 against the signal processing device 30 . The interference of electromagnetic fields generated in the signal processing device 30 is minimized in this way.
- both of the electrode shielding elements 20 and of the additional shielding means 21 is clear. This is associated, in particular, with the spatial configuration of the signal processing device 30 .
- the signal processing device 30 does not imply that the latter must undertake the entire extent of the processing of the measurement signals.
- the signal processing can also run only partially in the illustrated signal processing device 30 . Further signal processing devices arranged removed from the sensor system can be connected downstream of the illustrated signal processing device 30 .
- the additional shielding means 21 need not necessarily be designed in one piece.
- a hybrid design comprising individual shielding elements is also possible.
- the passage openings for the signal lines 4 can likewise be of variable design in order to fulfil different requirements placed on shielding between signal processing device 30 and the electrode device 10 .
- the signal processing device 30 illustrated as a unitary component in FIGS. 1 a and 1 b can be constructed from a plurality of spatially separate subelements. Individual ones of these subelements, or all of them can be surrounded by the additional shielding means 21 in different or the same compartments.
- FIG. 2 shows a schematic equivalent circuit diagram of the sensor system according to the invention.
- the electrode device 10 has an electrode capacitance C with respect to a measurement object Q that acts as a source of electromagnetic signals having a biobiological origin.
- This charge which is itself also time-dependent given a time-dependent source Q, reaches an operational amplifier, acting as an impedance converter 31 , of the signal processing device 30 .
- This impedance converter 31 has an input impedance Zi. All the resistive, capacitive and inductive external contributions of the environment, and the internal input impedance of the impedance converter 31 are combined in this input impedance Zi.
- the external part of the impedance Zi is intended to have as small as possible a capacitive and inductive and as high as possible a resistive fraction.
- the impedance converter 31 converts its input signal to such a small output impedance that conventional circuits 32 can subsequently be used for the further signal processing.
- the output signal of the impedance converter 31 constitutes the potential for the electrode shielding element 20 . This potential is denoted as guard potential in the case of commercially available guard electrode systems.
- parasitic signals occur that can be coupled in via a parasitic shielding capacitor Cg acting between electrode device 10 and electrode shielding element 20 , via a parasitic first shielding capacitor Cs 1 acting between electrode shielding element 20 and the shielding means 21 , and via a parasitic second shielding capacitor Cs 2 acting between electrode device 10 and the shielding means 21 .
- the parasitic capacitor Cg can be influenced via the dielectric properties of the medium arranged between electrode device 10 and electrode shielding element 20 .
- a corresponding statement is, of course, also valid for the parasitic capacitors Cs 1 and Cs 2 .
- the processed signal can be combined together with the output line of the impedance converter 31 in order to generate the potential for the electrode shielding element (guard potential) from a suitable logic operation.
- the parameters of the signal processing determine which type of signal logic operation (for example subtraction, addition etc.) is suitable for generating the guard potential.
- the dynamics range of the sensor system can also be increased in the way illustrated above.
- FIGS. 3 a to 3 c Different variants of the design of the electrode device 10 are illustrated in FIGS. 3 a to 3 c .
- Each of the three variants shown comprises a plurality of electrode elements 100 .
- FIG. 3 a shows a structure, interlocking in a finger-like fashion, of two comb-like electrode elements 100 .
- FIG. 3 c the electrode device 10 is designed in the form of five electrode elements 100 arranged as concentrically arranged rings of different diameter.
- the effect of external charges in the environment of the sensor system and of the electrode device 10 of the sensor system is to generate on the electrode device 10 or the individual electrode elements 100 of the electrode device 10 static charges that collect there and lead to static charging of the electrode device 10 .
- static charging of the electrode device 10 or of the electrode elements 100 of the electrode device 10 greatly impairs the dynamic range of the sensor system for receiving the electromagnetic signals from the measurement object Q, and reduces the signal-to-noise ratio of the sensor system that can be achieved.
- the detection of electromagnetic signals from the measurement object Q is attended by charge transfers on the electrode device 10 . If an electromagnetic signal to be detected passes from the measurement object Q to the electrode device 10 , the electromagnetic signal effects a charge transfer on the electrode device 10 , induces a current and therefore a signal that is processed in the signal processing device 30 . If, however, static charges are present on the electrode device 10 as a consequence of external charges in the environment of the sensor system, this has the effect that the dynamic range of the electrode device 10 is reduced for the electromagnetic signal from the measurement object Q that is actually to be detected and, in addition, interference signals are more strongly superposed on the electromagnetic signal.
- the static charge located on the electrode device 10 exerts a substantial influence on the interference of the electromagnetic signal to be received from the measurement object Q, owing to movement artefacts caused by the movement of the electrode device 10 relative to the measurement object Q.
- the change in the signal received by the electrode device 10 as a function of the distance of the electrode device 10 from the measurement object Q can be described by the following equation:
- the first term represents the change in the voltage U of the electrode device 10 with the spacing d between the electrode device 10 and the Measurement object Q
- the second term represents the change in the charge Q with the spacing d
- the third term represents the change in the electrode capacitance C with the spacing d.
- the second and third term of equation (1) must vanish, that is to say make no contribution, and so the signal U is independent of the change in the electrode capacitance C relative to the distance d between the electrode device 10 and the measurement object Q.
- the third term is proportional to the charge Q collected on the electrode device 10 . The suppression of the charge Q collected on the electrode device 10 is therefore attended by the reduction of movement artefacts interfering with the received signal.
- a feedback is arranged in the sensor system between the output of the signal processing device 30 and the electrode device 10 .
- a compensation impedance that is designed as a capacitor Ck is provided for this purpose.
- This compensation impedance acts between the electrode device 10 and the signal output of the signal processing device.
- This compensation impedance Ck can, as illustrated in FIG. 2 , be capacitive, but also resistive or inductive.
- the dynamic range of the sensor system can be enlarged by the provision of the compensation impedance Ck.
- FIG. 4 illustrates a further embodiment of a compensation circuit using a compensation impedance Ck.
- the compensation circuit illustrated has an electrode device 10 , an impedance converter 31 and a circuit 32 that serves for feeding the signal from the output of the signal processing device 30 back to the electrode device 10 via the compensation impedance Ck.
- the circuit 31 comprises two stages, of which the first stage, comprising the resistors R 1 , R 2 , R 3 and Rt, the capacitors C 1 , Ct and the operation amplifier O 1 , constitutes a second order lowpass filter, and the second stage, comprising resistors R 4 , R 5 , R 6 , R 7 , capacitor C 2 and the operation amplifier O 2 , constitutes a control circuit for feeding the signal back to the electrode device 10 .
- a signal detected by the electrode device 10 is then led via the impedance converter 31 to the lowpass arrangement, filtered by the lowpass arrangement and fed back to the electrode device 10 via the control circuit and the compensation impedance formed by the capacitor Ck.
- the effect of the compensation impedance Ck is that charge can be exchanged between the electrode device 10 and the output of the signal processing device 30 .
- a lowpass-filtered output signal of opposite sign can be fed back to the electrode device 10 via the compensation impedance Ck, such that it is precisely the charge quantity opposite to the charge quantity collected on the electrode device 10 that is coupled into the electrode device 10 .
- the cut-off frequency of the lowpass arrangement can be selected to be so small that the lowpass-filtered signal is essentially static in nature, and so it is also only the low frequency, essentially static components of the output signal that are fed back to the electrode device 10 .
- the cut-off frequency of the lowpass arrangement can in this case sensibly be of the order of magnitude of 200 mHz, and thus much below the frequency range of the electromagnetic signals to be detected from a measurement object Q.
- a most far reaching complete suppression of the static charging of the electrode device 10 can be achieved by means of the compensation impedance Ck illustrated in FIG. 2 and in FIG. 4 . It is thereby possible to improve the dynamic range of the electrode device 10 , and to enlarge the achievable signal-to-noise ratio of the sensor system.
- a method is provided by means of which it is possible to minimize the influence of movement artefacts on a measured electromagnetic signal from a measurement object Q as effected by a relative movement of the capacitive electrode device 10 with reference to the measurement object Q.
- a sensor system with an electrode device 10 or a measuring device having a multiplicity of sensor systems and electrode devices 10 , is/are fitted on a measurement object Q, an electrical alternating signal is coupled into the measurement object via the electrode device 10 , the alternating signal coupled in is evaluated, and the temporal change in the electrode capacitance C of the electrode device 10 of the sensor system is thereby determined.
- the determination of the electrode capacitance C is performed separately in this case for each electrode device 10 of each sensor system such that the movement of each electrode device 10 can be compensated separately.
- the compensation is performed by taking account of the temporal change in the electrode capacitance and evaluating the measurement signals of each sensor system, and the movement artefacts caused by movement are thereby removed from the measurement signal by calculation.
- FIG. 5 A schematic sketch of the arrangement of an electrode device 10 on a measurement object Q is illustrated in FIG. 5 .
- the electrode device 10 lies at a distance d(t) from the measurement object Q, the distance d(t) being temporally variable, and therefore the capacitance C, formed by the electrode device 10 with the measurement object Q, is also temporally variable.
- a temporally variable alternating signal a(t) is applied to the electrode device 10 , and the response signal b(t) of the alternating signal (a(t) is measured.
- the alternating signal a(t) is in this case a carrier signal at a specific frequency, for example 300 Hz, while the response signal b(t) corresponds to the modulation of the alternating signal a(t) by the movement of the electrode device 10 relative to the measurement object Q.
- the movement of the electrode device 10 relative to the measurement object Q is correlated in this case with the temporal change in the electrode capacitance C, such that the information relating to the temporal change in the electrode capacitance C is contained in the response signal b(t) formed by the modulated alternating signal a(t).
- the response signal b(t) corresponds to the amplitude modulation of the alternating signal a(t) as caused by the electrode capacitance C changing with the distance.
- the alternating signal a(t) is modulated in frequency or phase by the changing electrode capacitance C, or by other known modulation methods, it being possible to this end to make use of known circuits in which the electrode capacitance C functions in each case as a modulating component.
- a feed path for feeding the alternating signal a(t) into each electrode device 10 is superfluous in this case, and so, as illustrated in FIG. 2 , the sensor system need only have a receiving path, that is to say means 30 , 31 , 32 for receiving a signal.
- Such an electrode arrangement can, for example, be designed as illustrated in FIGS. 3 a to c , in which case one of the electrode elements 100 would then serve as reference electrode, and the other electrode elements 100 as receiving electrodes.
- the reference electrode can generally be fitted on the measurement object Q in resistive, inductive or capacitive fashion, in order to feed an alternating signal a(t) into the measurement object Q. It is also conceivable to use a number of reference electrodes that feed in alternating signals of different frequency, an electrode device 10 respectively receiving an alternating signal a(t) at a frequency from which it is then possible to draw conclusions relating to the movement of the respective electrode device 10 relative to the measurement object Q.
- FIG. 6 illustrates an example of a response signal b(t) received by an electrode device 10 .
- Shown here is the frequency spectrum of the response signal b(t), which corresponds to the Fourier transformed F ⁇ b(t) ⁇ of the response signal b(t).
- an alternating signal a(t) is coupled in via a reference electrode that is fitted on the measurement object Q in a resistive fashion, the electrode device 10 executing a movement at a frequency of 10 Hz relative to the measurement object Q.
- FIG. 7 shows a measured response signal b(t) (bottom in FIG. 7 ) and a movement signal B(t) (top in FIG. 7 ) that is calculated from the response signal b(t) and is correlated with the temporal change in the electrode capacitance C, and therefore contains the information relating to the temporal change in the electrode device 10 relative to the measurement object Q.
- the movement signal B(t) is derived here from the response signal b(t) by subjecting the response signal b(t) to highpass filtering, and the components of the electromagnetic signal having a biobiological origin that is to be detected from the measurement object Q, which lie in a frequency range below the frequency of the alternating signal a(t), in this case 300 Hz, are suppressed.
- the highpass filtered response signal b(t) is demodulated, and so the component of the original alternating signal a(t) is removed from the response signal b(t) by calculation and the movement signal B(t) is thereby determined. Since the movement signal B(t) is correlated with the temporal change in the electrode capacitance C, and thus contains the information relating to the relative temporal change in the electrode capacitance C as a function of the movement of the electrode device 10 relative to the measurement object Q, the movement signal B(t) can be further processed and can be used with the aid of known signal processing algorithms to compensate the movement artefacts in the detected electromagnetic measurement signal having a biobiological origin.
- the compensation of the movement artefacts can be carried out in this case either in a post processing step downstream of the actual measurement, or else run in real time, given a correspondingly more powerful signal processing device 30 , during the measurement for the purpose of direct compensation of the movement artefacts.
- FIG. 8 shows the fundamental sequence of the method for minimizing the influence of movement artefacts by using the sensor system according to the invention, in the case of which the change in the electrode capacitance C of the electrode device 10 is taken into account when evaluating the measurement signals of the sensor system or of the measuring device.
- FIG. 9 The fundamental sequence of a further method for minimizing the influence of movement artefacts is illustrated in FIG. 9 .
- the sensor system or the measuring device is firstly arranged on a measurement object, the sensor system or the measuring device being provided with a position measuring system for determining the position of the sensor system or measuring device. Subsequently, the position parameters of the position of the sensor system or the sensor systems are determined relative to the measurement object during the measurement, and the determined position parameters are taken into account to compensate movement artefacts in the measurement signal.
Landscapes
- Life Sciences & Earth Sciences (AREA)
- Health & Medical Sciences (AREA)
- Medical Informatics (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
Description
Claims (31)
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102004063249A DE102004063249A1 (en) | 2004-12-23 | 2004-12-23 | Sensor system and method for the capacitive measurement of electromagnetic signals of biological origin |
DE102004063249.9 | 2004-12-23 | ||
DE102004063249 | 2004-12-23 | ||
PCT/DE2005/002319 WO2006066566A2 (en) | 2004-12-23 | 2005-12-23 | Sensor system and methods for the capacitive measurement of electromagnetic signals having a biological origin |
Publications (3)
Publication Number | Publication Date |
---|---|
US20100060300A1 US20100060300A1 (en) | 2010-03-11 |
US20110248729A2 US20110248729A2 (en) | 2011-10-13 |
US8193821B2 true US8193821B2 (en) | 2012-06-05 |
Family
ID=36202212
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/722,495 Active 2027-12-04 US8193821B2 (en) | 2004-12-23 | 2005-12-23 | Sensor system and methods for the capacitive measurement of electromagnetic signals having a biological origin |
Country Status (6)
Country | Link |
---|---|
US (1) | US8193821B2 (en) |
EP (1) | EP1827218B1 (en) |
JP (1) | JP4831700B2 (en) |
AT (1) | ATE521280T1 (en) |
DE (1) | DE102004063249A1 (en) |
WO (1) | WO2006066566A2 (en) |
Cited By (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110166434A1 (en) * | 2008-07-07 | 2011-07-07 | Gaetano Gargiulo | System for sensing electrophysiological signals |
EP2727528A1 (en) | 2012-11-05 | 2014-05-07 | CSEM Centre Suisse d'Electronique et de Microtechnique SA | Method for bio impedance measurement |
US8838198B2 (en) | 2008-11-14 | 2014-09-16 | Neuronetrix Solutions, Llc | Electrode system |
US8937481B2 (en) | 2009-05-29 | 2015-01-20 | Koninklijke Philips N.V. | Capacitive sensing apparatus |
US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
WO2015077886A1 (en) | 2013-11-27 | 2015-06-04 | Zengar Institute Inc. | Ultra high impedance sensor with applications in neurosensing |
US9059532B2 (en) | 2010-06-25 | 2015-06-16 | Nox Medical | Biometric belt connector |
US9192316B2 (en) | 2009-05-15 | 2015-11-24 | Nox Medical | Systems and methods using flexible capacitive electrodes for measuring biosignals |
US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
US9597010B2 (en) | 2005-04-28 | 2017-03-21 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
US9814426B2 (en) | 2012-06-14 | 2017-11-14 | Medibotics Llc | Mobile wearable electromagnetic brain activity monitor |
US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
US10379074B2 (en) | 2017-12-21 | 2019-08-13 | NeoTek Energy, Inc. | System and method for shielded chemical sensing using a fine-line shielded sensing structure |
US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
US10588550B2 (en) | 2013-11-06 | 2020-03-17 | Nox Medical | Method, apparatus, and system for measuring respiratory effort |
US10869619B2 (en) | 2016-08-19 | 2020-12-22 | Nox Medical | Method, apparatus, and system for measuring respiratory effort of a subject |
US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
US11602282B2 (en) | 2017-09-08 | 2023-03-14 | Nox Medical Ehf | System and method for non-invasively determining an internal component of respiratory effort |
US11896386B2 (en) | 2017-06-02 | 2024-02-13 | Nox Medical Ehf | Coherence-based method, apparatus, and system for identifying corresponding signals of a physiological study |
Families Citing this family (95)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2009517117A (en) * | 2005-11-25 | 2009-04-30 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Biometric sensor |
EP2037999B1 (en) | 2006-07-07 | 2016-12-28 | Proteus Digital Health, Inc. | Smart parenteral administration system |
WO2008012723A2 (en) * | 2006-07-20 | 2008-01-31 | Philips Intellectual Property & Standards Gmbh | A detector for and a method of detecting electromagnetic radiation |
US8129629B2 (en) * | 2006-12-06 | 2012-03-06 | Siemens Aktiengesellschaft | Arrangement for reducing the field strength on an electrode |
US20090024049A1 (en) | 2007-03-29 | 2009-01-22 | Neurofocus, Inc. | Cross-modality synthesis of central nervous system, autonomic nervous system, and effector data |
US9886981B2 (en) | 2007-05-01 | 2018-02-06 | The Nielsen Company (Us), Llc | Neuro-feedback based stimulus compression device |
US8386312B2 (en) | 2007-05-01 | 2013-02-26 | The Nielsen Company (Us), Llc | Neuro-informatics repository system |
US20090328089A1 (en) * | 2007-05-16 | 2009-12-31 | Neurofocus Inc. | Audience response measurement and tracking system |
US8392253B2 (en) | 2007-05-16 | 2013-03-05 | The Nielsen Company (Us), Llc | Neuro-physiology and neuro-behavioral based stimulus targeting system |
US20090024449A1 (en) * | 2007-05-16 | 2009-01-22 | Neurofocus Inc. | Habituation analyzer device utilizing central nervous system, autonomic nervous system and effector system measurements |
US8494905B2 (en) | 2007-06-06 | 2013-07-23 | The Nielsen Company (Us), Llc | Audience response analysis using simultaneous electroencephalography (EEG) and functional magnetic resonance imaging (fMRI) |
US20090030287A1 (en) * | 2007-06-06 | 2009-01-29 | Neurofocus Inc. | Incented response assessment at a point of transaction |
US20090036755A1 (en) * | 2007-07-30 | 2009-02-05 | Neurofocus, Inc. | Entity and relationship assessment and extraction using neuro-response measurements |
KR20100038107A (en) | 2007-07-30 | 2010-04-12 | 뉴로포커스, 인크. | Neuro-response stimulus and stimulus attribute resonance estimator |
US20110105874A1 (en) * | 2007-08-20 | 2011-05-05 | Koninklijke Philips Electronics N.V. | Method for measuring body parameters |
KR20100047865A (en) | 2007-08-28 | 2010-05-10 | 뉴로포커스, 인크. | Consumer experience assessment system |
US8386313B2 (en) | 2007-08-28 | 2013-02-26 | The Nielsen Company (Us), Llc | Stimulus placement system using subject neuro-response measurements |
US8635105B2 (en) | 2007-08-28 | 2014-01-21 | The Nielsen Company (Us), Llc | Consumer experience portrayal effectiveness assessment system |
US8392255B2 (en) | 2007-08-29 | 2013-03-05 | The Nielsen Company (Us), Llc | Content based selection and meta tagging of advertisement breaks |
US20090083129A1 (en) | 2007-09-20 | 2009-03-26 | Neurofocus, Inc. | Personalized content delivery using neuro-response priming data |
US8494610B2 (en) | 2007-09-20 | 2013-07-23 | The Nielsen Company (Us), Llc | Analysis of marketing and entertainment effectiveness using magnetoencephalography |
US9125979B2 (en) | 2007-10-25 | 2015-09-08 | Proteus Digital Health, Inc. | Fluid transfer port information system |
US8419638B2 (en) | 2007-11-19 | 2013-04-16 | Proteus Digital Health, Inc. | Body-associated fluid transport structure evaluation devices |
US8517383B2 (en) * | 2008-06-20 | 2013-08-27 | Pure Imagination, LLC | Interactive game board system incorporating capacitive sensing and identification of game pieces |
WO2010023615A1 (en) * | 2008-08-29 | 2010-03-04 | Koninklijke Philips Electronics N.V. | Compensation of motion artifacts in capacitive measurement of electrophysiological signals |
US20100152602A1 (en) * | 2008-12-17 | 2010-06-17 | Ross Colin A | Whole body electromagnetic detection system |
US8464288B2 (en) | 2009-01-21 | 2013-06-11 | The Nielsen Company (Us), Llc | Methods and apparatus for providing personalized media in video |
US9357240B2 (en) | 2009-01-21 | 2016-05-31 | The Nielsen Company (Us), Llc | Methods and apparatus for providing alternate media for video decoders |
US8270814B2 (en) | 2009-01-21 | 2012-09-18 | The Nielsen Company (Us), Llc | Methods and apparatus for providing video with embedded media |
US20100250325A1 (en) | 2009-03-24 | 2010-09-30 | Neurofocus, Inc. | Neurological profiles for market matching and stimulus presentation |
DE102009019242B4 (en) | 2009-04-30 | 2014-09-11 | Technische Universität Carolo-Wilhelmina Zu Braunschweig | Medical diagnostic device and method for determining a spatially resolved image information |
EP2453792B1 (en) * | 2009-07-13 | 2017-05-17 | Koninklijke Philips N.V. | Electro-physiological measurement with reduced motion artifacts |
US20110046502A1 (en) * | 2009-08-20 | 2011-02-24 | Neurofocus, Inc. | Distributed neuro-response data collection and analysis |
US20110046473A1 (en) * | 2009-08-20 | 2011-02-24 | Neurofocus, Inc. | Eeg triggered fmri signal acquisition |
US8655437B2 (en) | 2009-08-21 | 2014-02-18 | The Nielsen Company (Us), Llc | Analysis of the mirror neuron system for evaluation of stimulus |
US10987015B2 (en) | 2009-08-24 | 2021-04-27 | Nielsen Consumer Llc | Dry electrodes for electroencephalography |
US9560984B2 (en) | 2009-10-29 | 2017-02-07 | The Nielsen Company (Us), Llc | Analysis of controlled and automatic attention for introduction of stimulus material |
US8209224B2 (en) | 2009-10-29 | 2012-06-26 | The Nielsen Company (Us), Llc | Intracluster content management using neuro-response priming data |
US20110106750A1 (en) | 2009-10-29 | 2011-05-05 | Neurofocus, Inc. | Generating ratings predictions using neuro-response data |
US8335715B2 (en) | 2009-11-19 | 2012-12-18 | The Nielsen Company (Us), Llc. | Advertisement exchange using neuro-response data |
US8335716B2 (en) | 2009-11-19 | 2012-12-18 | The Nielsen Company (Us), Llc. | Multimedia advertisement exchange |
US9405408B2 (en) | 2010-01-15 | 2016-08-02 | Creator Technology B.V. | Trace pattern for touch-sensing application |
DE102010005551A1 (en) | 2010-01-22 | 2011-07-28 | Badower, Yakob, Dipl.-Ing. | Sensor system for non-invasive detection of e.g. electrocardiogram signals of biological elements in head of human, has body contact electrodes coupled to shielding device for providing interference signals to shielding device |
EP2531096A4 (en) | 2010-02-01 | 2013-09-11 | Proteus Digital Health Inc | Two-wrist data gathering system |
WO2011133548A2 (en) | 2010-04-19 | 2011-10-27 | Innerscope Research, Inc. | Short imagery task (sit) research method |
US8655428B2 (en) | 2010-05-12 | 2014-02-18 | The Nielsen Company (Us), Llc | Neuro-response data synchronization |
US20110301486A1 (en) * | 2010-06-03 | 2011-12-08 | Cordial Medical Europe | Measurement of auditory evoked responses |
DE102010023369A1 (en) | 2010-06-10 | 2010-12-30 | Daimler Ag | Vehicle i.e. lorry, has electrode built in sensor, shielding, mass and isolating layers directly lying one upon another for capacitive measurement of biological signals of occupant in seat and/or couch |
DE102010017415A1 (en) | 2010-06-17 | 2011-12-22 | Yakob Badower | Sensor system i.e. head sensor system, for non-invasive detecting e.g. ECG signals of biological origin mounted on head of human body, has measuring electrodes partly formed of thermoplastic elastomer |
JP2012005640A (en) * | 2010-06-24 | 2012-01-12 | Ritsumeikan | Electrode unit for electroencephalography |
US8482546B2 (en) * | 2010-06-30 | 2013-07-09 | Cypress Semiconductor Corporation | Self shielding capacitance sensing panel |
JP5593926B2 (en) * | 2010-07-29 | 2014-09-24 | ソニー株式会社 | Power feeding system, power feeding device and electronic device |
US8392250B2 (en) | 2010-08-09 | 2013-03-05 | The Nielsen Company (Us), Llc | Neuro-response evaluated stimulus in virtual reality environments |
US8392251B2 (en) | 2010-08-09 | 2013-03-05 | The Nielsen Company (Us), Llc | Location aware presentation of stimulus material |
DE102010034192A1 (en) * | 2010-08-12 | 2012-02-16 | Capical Gmbh | ECG handset |
US8396744B2 (en) | 2010-08-25 | 2013-03-12 | The Nielsen Company (Us), Llc | Effective virtual reality environments for presentation of marketing materials |
JP5569939B2 (en) * | 2010-09-27 | 2014-08-13 | 株式会社ワコム | Variable capacitor, position indicator and input device |
JP5605153B2 (en) | 2010-10-15 | 2014-10-15 | ソニー株式会社 | Power supply device, power supply method, and power supply system |
JP5625723B2 (en) * | 2010-10-15 | 2014-11-19 | ソニー株式会社 | Electronic device, power supply method and power supply system |
JP5668604B2 (en) * | 2011-05-31 | 2015-02-12 | 株式会社デンソー | ECG detector |
JP5802334B2 (en) * | 2011-08-24 | 2015-10-28 | ヴェーデクス・アクティーセルスカプ | EEG monitor with capacitive electrode and electroencephalogram monitoring method |
WO2013072839A2 (en) * | 2011-11-15 | 2013-05-23 | Koninklijke Philips Electronics N.V. | Dual-mode capacitive measurement |
DE102012014219A1 (en) | 2012-02-15 | 2013-08-22 | Alexander von Lühmann | Capacitive sensor system for measurement of electromagnetic bio-signals, has two capacitive sensors which are provided for measurement of bioelectric field, and for detecting relative movement of two relatively movable elements |
US9292858B2 (en) | 2012-02-27 | 2016-03-22 | The Nielsen Company (Us), Llc | Data collection system for aggregating biologically based measures in asynchronous geographically distributed public environments |
US9569986B2 (en) | 2012-02-27 | 2017-02-14 | The Nielsen Company (Us), Llc | System and method for gathering and analyzing biometric user feedback for use in social media and advertising applications |
US9451303B2 (en) | 2012-02-27 | 2016-09-20 | The Nielsen Company (Us), Llc | Method and system for gathering and computing an audience's neurologically-based reactions in a distributed framework involving remote storage and computing |
US9060671B2 (en) | 2012-08-17 | 2015-06-23 | The Nielsen Company (Us), Llc | Systems and methods to gather and analyze electroencephalographic data |
US9320450B2 (en) | 2013-03-14 | 2016-04-26 | The Nielsen Company (Us), Llc | Methods and apparatus to gather and analyze electroencephalographic data |
KR102172486B1 (en) * | 2013-08-08 | 2020-10-30 | 삼성전자주식회사 | Flexible capacitive coupling active electrode and bio signal measuring device |
US9622702B2 (en) | 2014-04-03 | 2017-04-18 | The Nielsen Company (Us), Llc | Methods and apparatus to gather and analyze electroencephalographic data |
WO2016150594A1 (en) * | 2015-03-23 | 2016-09-29 | Iee International Electronics & Engineering S.A. | Capacitive sensing system with hardware diagnostics concept for detection of sensor interruption |
US9936250B2 (en) | 2015-05-19 | 2018-04-03 | The Nielsen Company (Us), Llc | Methods and apparatus to adjust content presented to an individual |
US10568572B2 (en) | 2016-03-14 | 2020-02-25 | The Nielsen Company (Us), Llc | Headsets and electrodes for gathering electroencephalographic data |
CN108882886B (en) * | 2016-03-29 | 2023-02-28 | 小利兰·斯坦福大学托管委员会 | Proximity sensor circuit and related sensing method |
WO2017189748A1 (en) * | 2016-04-29 | 2017-11-02 | Freer Logic, Inc. | Non-contact body and head-based monitoring of brain electrical activity |
DE102016112391A1 (en) * | 2016-07-06 | 2018-01-25 | Capical Gmbh | treatment table |
US10605832B2 (en) * | 2016-11-11 | 2020-03-31 | Fluke Corporation | Sensor subsystems for non-contact voltage measurement devices |
US10352967B2 (en) | 2016-11-11 | 2019-07-16 | Fluke Corporation | Non-contact electrical parameter measurement systems |
US10139435B2 (en) | 2016-11-11 | 2018-11-27 | Fluke Corporation | Non-contact voltage measurement system using reference signal |
EP3231357B1 (en) * | 2017-02-06 | 2019-04-03 | Polar Electro Oy | Emi protection for physiological measurements |
JP6909968B2 (en) * | 2017-06-30 | 2021-07-28 | パナソニックIpマネジメント株式会社 | Biopotential measuring device, electroencephalograph, capacitance control method and program |
ES2835779T3 (en) * | 2017-07-17 | 2021-06-23 | Mettler Toledo Gmbh | Procedure and device for monitoring and / or determining the status of a measurement probe |
CN107576694A (en) * | 2017-10-17 | 2018-01-12 | 湖南科技学院 | A kind of comb capacitance diaper urine detector |
GB2568478B (en) * | 2017-11-15 | 2020-05-20 | 4T2 Sensors Ltd | Apparatus for monitoring a fluid |
US10161667B1 (en) * | 2017-11-15 | 2018-12-25 | Haier Us Appliance Solutions, Inc. | Refrigerator appliance having a defrost chamber |
US10509063B2 (en) | 2017-11-28 | 2019-12-17 | Fluke Corporation | Electrical signal measurement device using reference signal |
US10775409B2 (en) | 2018-05-09 | 2020-09-15 | Fluke Corporation | Clamp probe for non-contact electrical parameter measurement |
US10551416B2 (en) * | 2018-05-09 | 2020-02-04 | Fluke Corporation | Multi-sensor configuration for non-contact voltage measurement devices |
US10677876B2 (en) | 2018-05-09 | 2020-06-09 | Fluke Corporation | Position dependent non-contact voltage and current measurement |
US10746767B2 (en) | 2018-05-09 | 2020-08-18 | Fluke Corporation | Adjustable length Rogowski coil measurement device with non-contact voltage measurement |
US10557875B2 (en) | 2018-05-09 | 2020-02-11 | Fluke Corporation | Multi-sensor scanner configuration for non-contact voltage measurement devices |
US10908188B2 (en) | 2018-05-11 | 2021-02-02 | Fluke Corporation | Flexible jaw probe for non-contact electrical parameter measurement |
US10802072B2 (en) | 2018-05-11 | 2020-10-13 | Fluke Corporation | Non-contact DC voltage measurement device with oscillating sensor |
CN114831641A (en) * | 2021-02-02 | 2022-08-02 | 武汉联影智融医疗科技有限公司 | Human body signal acquisition device |
DE102021206856A1 (en) | 2021-06-30 | 2023-01-05 | Siemens Healthcare Gmbh | Layer structure of a sensor for capacitive measurement of bioelectrical signals |
Citations (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3510195A1 (en) | 1985-03-21 | 1986-09-25 | Philips Patentverwaltung Gmbh, 2000 Hamburg | Method for generating a movement signal and nuclear spin tomograph for such a method |
DE19749710A1 (en) | 1997-10-31 | 1999-05-06 | Biotronik Mess & Therapieg | Electrostimulator |
WO2002013676A2 (en) | 2000-08-11 | 2002-02-21 | Sam Technology, Inc. | Ceramic single-plate capacitor eeg electrode |
US20030036691A1 (en) | 2000-08-10 | 2003-02-20 | Stanaland Thomas G. | Capacitively coupled electrode system with variable capacitance for sensing potentials at the surface of tissue |
WO2003048789A2 (en) | 2001-12-07 | 2003-06-12 | Clark Terence D | Electrodynamic sensors and applications thereof |
US20040073104A1 (en) | 2001-02-23 | 2004-04-15 | Riccardo Brun Del Re | Enhanced pickup-electrode |
EP1428471A2 (en) | 2002-11-18 | 2004-06-16 | HONDA MOTOR CO., Ltd. | Optical measuring apparatus and method |
WO2004052190A1 (en) | 2002-12-10 | 2004-06-24 | Koninklijke Philips Electronics N.V. | A wearable device for bioelectrical interaction with motion artifact correction means |
US6807438B1 (en) | 1999-08-26 | 2004-10-19 | Riccardo Brun Del Re | Electric field sensor |
US20040254435A1 (en) | 2003-06-11 | 2004-12-16 | Robert Mathews | Sensor system for measuring biopotentials |
-
2004
- 2004-12-23 DE DE102004063249A patent/DE102004063249A1/en not_active Ceased
-
2005
- 2005-12-23 JP JP2007547175A patent/JP4831700B2/en active Active
- 2005-12-23 EP EP05850193A patent/EP1827218B1/en active Active
- 2005-12-23 WO PCT/DE2005/002319 patent/WO2006066566A2/en active Application Filing
- 2005-12-23 US US11/722,495 patent/US8193821B2/en active Active
- 2005-12-23 AT AT05850193T patent/ATE521280T1/en active
Patent Citations (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3510195A1 (en) | 1985-03-21 | 1986-09-25 | Philips Patentverwaltung Gmbh, 2000 Hamburg | Method for generating a movement signal and nuclear spin tomograph for such a method |
DE19749710A1 (en) | 1997-10-31 | 1999-05-06 | Biotronik Mess & Therapieg | Electrostimulator |
US6807438B1 (en) | 1999-08-26 | 2004-10-19 | Riccardo Brun Del Re | Electric field sensor |
US20030036691A1 (en) | 2000-08-10 | 2003-02-20 | Stanaland Thomas G. | Capacitively coupled electrode system with variable capacitance for sensing potentials at the surface of tissue |
WO2002013676A2 (en) | 2000-08-11 | 2002-02-21 | Sam Technology, Inc. | Ceramic single-plate capacitor eeg electrode |
US6445940B1 (en) | 2000-08-11 | 2002-09-03 | Sam Technology, Inc. | Ceramic single-plate capacitor EEG electrode |
US20040073104A1 (en) | 2001-02-23 | 2004-04-15 | Riccardo Brun Del Re | Enhanced pickup-electrode |
WO2003048789A2 (en) | 2001-12-07 | 2003-06-12 | Clark Terence D | Electrodynamic sensors and applications thereof |
EP1428471A2 (en) | 2002-11-18 | 2004-06-16 | HONDA MOTOR CO., Ltd. | Optical measuring apparatus and method |
WO2004052190A1 (en) | 2002-12-10 | 2004-06-24 | Koninklijke Philips Electronics N.V. | A wearable device for bioelectrical interaction with motion artifact correction means |
US20040254435A1 (en) | 2003-06-11 | 2004-12-16 | Robert Mathews | Sensor system for measuring biopotentials |
US6961601B2 (en) * | 2003-06-11 | 2005-11-01 | Quantum Applied Science & Research, Inc. | Sensor system for measuring biopotentials |
Non-Patent Citations (3)
Title |
---|
Harland C J et al: "Remote detection of human electroencephalalograms using ultrahigh input impedance electric potential sensors" Applied Physics Letters AIP USA, vol. 81, No. 17, Oct. 21, 2002, pp. 3284-3286. |
Japanese Foreign Office Action mailed Aug. 10, 2010 for Japanese application 2007-547175. |
Searle A et al: "A direct comparison of wet, dry and insulting bioelectric recording electrodes; A comparison of bioelectrode performance" Physiological Measurement, Institute of Physics Publishing, Bristol, GB, vol. 21, No. 2, May 1, 2000, pp. 271-283. |
Cited By (35)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9597010B2 (en) | 2005-04-28 | 2017-03-21 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US20110166434A1 (en) * | 2008-07-07 | 2011-07-07 | Gaetano Gargiulo | System for sensing electrophysiological signals |
US8838198B2 (en) | 2008-11-14 | 2014-09-16 | Neuronetrix Solutions, Llc | Electrode system |
US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
US10548497B2 (en) | 2009-05-15 | 2020-02-04 | Nox Medical | Systems and methods using flexible capacitive electrodes for measuring biosignals |
US9192316B2 (en) | 2009-05-15 | 2015-11-24 | Nox Medical | Systems and methods using flexible capacitive electrodes for measuring biosignals |
US8937481B2 (en) | 2009-05-29 | 2015-01-20 | Koninklijke Philips N.V. | Capacitive sensing apparatus |
US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
US10376218B2 (en) | 2010-02-01 | 2019-08-13 | Proteus Digital Health, Inc. | Data gathering system |
US9537246B2 (en) | 2010-06-25 | 2017-01-03 | Nox Medical | Biometric belt connector |
US9059532B2 (en) | 2010-06-25 | 2015-06-16 | Nox Medical | Biometric belt connector |
US10141675B2 (en) | 2010-06-25 | 2018-11-27 | Nox Medical | Biometric belt connector |
US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
US9814426B2 (en) | 2012-06-14 | 2017-11-14 | Medibotics Llc | Mobile wearable electromagnetic brain activity monitor |
EP2727528A1 (en) | 2012-11-05 | 2014-05-07 | CSEM Centre Suisse d'Electronique et de Microtechnique SA | Method for bio impedance measurement |
US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
US11741771B2 (en) | 2013-03-15 | 2023-08-29 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
US9787511B2 (en) | 2013-09-20 | 2017-10-10 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US10097388B2 (en) | 2013-09-20 | 2018-10-09 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US11102038B2 (en) | 2013-09-20 | 2021-08-24 | Otsuka Pharmaceutical Co., Ltd. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US10498572B2 (en) | 2013-09-20 | 2019-12-03 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
US10588550B2 (en) | 2013-11-06 | 2020-03-17 | Nox Medical | Method, apparatus, and system for measuring respiratory effort |
US10660575B2 (en) | 2013-11-27 | 2020-05-26 | Zengar Institute Inc. | Ultra high impedance sensor with applications in neurosensing |
WO2015077886A1 (en) | 2013-11-27 | 2015-06-04 | Zengar Institute Inc. | Ultra high impedance sensor with applications in neurosensing |
US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
US11950615B2 (en) | 2014-01-21 | 2024-04-09 | Otsuka Pharmaceutical Co., Ltd. | Masticable ingestible product and communication system therefor |
US10869619B2 (en) | 2016-08-19 | 2020-12-22 | Nox Medical | Method, apparatus, and system for measuring respiratory effort of a subject |
US11896386B2 (en) | 2017-06-02 | 2024-02-13 | Nox Medical Ehf | Coherence-based method, apparatus, and system for identifying corresponding signals of a physiological study |
US11602282B2 (en) | 2017-09-08 | 2023-03-14 | Nox Medical Ehf | System and method for non-invasively determining an internal component of respiratory effort |
US10379074B2 (en) | 2017-12-21 | 2019-08-13 | NeoTek Energy, Inc. | System and method for shielded chemical sensing using a fine-line shielded sensing structure |
Also Published As
Publication number | Publication date |
---|---|
WO2006066566A2 (en) | 2006-06-29 |
DE102004063249A1 (en) | 2006-07-13 |
WO2006066566A3 (en) | 2006-09-21 |
JP4831700B2 (en) | 2011-12-07 |
US20110248729A2 (en) | 2011-10-13 |
JP2008525063A (en) | 2008-07-17 |
ATE521280T1 (en) | 2011-09-15 |
US20100060300A1 (en) | 2010-03-11 |
EP1827218A2 (en) | 2007-09-05 |
EP1827218B1 (en) | 2011-08-24 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8193821B2 (en) | Sensor system and methods for the capacitive measurement of electromagnetic signals having a biological origin | |
JP4875696B2 (en) | Method and apparatus for suppressing interference in electromagnetic multi-channel measurements | |
JP4738958B2 (en) | ECG measurement device | |
US9675298B2 (en) | Apparatus and method for measuring bioelectric signals | |
US20140249397A1 (en) | Differential non-contact biopotential sensor | |
EP2010053A2 (en) | System for measuring electric signals | |
US20110105874A1 (en) | Method for measuring body parameters | |
KR102083559B1 (en) | Electrode for living body, apparatus and method for processing biological signal | |
KR20150146328A (en) | Bioelectrode and biosignal processing apparatus and method using the same | |
Kuronen | Epic sensors in electrocardiogram measurement | |
Peng et al. | Non-contact ECG sensing employing gradiometer electrodes | |
Rakhmatulin et al. | Review Dry and Non-contact EEG Electrodes for 2010-2021 years | |
Weeks et al. | A novel sensor-array system for contactless electrocardiogram acquisition | |
JP2012005640A (en) | Electrode unit for electroencephalography | |
Ng et al. | A flexible capacitive electromyography biomedical sensor for wearable healthcare applications | |
Islam | Artifact characterization, detection and removal from neural signals | |
Teeramongkonrasmee et al. | Performance of a QRS detector on self-collected database using a handheld two-electrode ECG | |
KR102411675B1 (en) | sensor device | |
Peng et al. | Non-contact ECG employing signal compensation | |
WO2021090955A1 (en) | Biosignal detection device, heart rate signal detection server, vehicle, biosignal detection program, and heart rate signal detection program | |
Heuer et al. | Signal quality assessment for capacitive ECG monitoring systems using body-sensor-impedance | |
Khalili et al. | Motion artifacts in capacitive ECG monitoring systems: a review of existing models and reduction techniques | |
RU163596U1 (en) | HUMAN ELECTRIC CARDIOGRAPHY REGISTRATION DEVICE | |
CN112656428B (en) | Electronic equipment and method for acquiring human physiological signals by using non-embedded brain-computer interface | |
Casadei et al. | Online Skin-Electrode Contact Quality Monitoring in Wearable Devices: An EEG Application |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: FRAUNHOFER-GESELLSCHAFT ZUR FORDERUNG DER ANGEWAND Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:020281/0277 Owner name: TECHNISCHE UNIVERSITAT BRAUNSCHWEIG,GERMANY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:SCHILLING, MEINHARD;REEL/FRAME:020281/0282 Effective date: 20071122 Owner name: TECHNISCHE UNIVERSITAT BRAUNSCHWEIG, GERMANY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:SCHILLING, MEINHARD;REEL/FRAME:020281/0282 Effective date: 20071122 |
|
AS | Assignment |
Owner name: FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER AGNEWAN Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE NAMES OF FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V. AND TECHNISHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0277. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO THREE ORGANIZATIONS;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023351/0807 Owner name: TECHNISHE UNIVERSITAET BRAUNSCHWEIG,GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE NAMES OF FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V. AND TECHNISHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0277. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO THREE ORGANIZATIONS;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023351/0807 Owner name: CHARITE-UNIVERSITATSMEDIZIN BERLIN,GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE NAMES OF FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V. AND TECHNISHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0277. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO THREE ORGANIZATIONS;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023351/0807 Owner name: TECHNISHE UNIVERSITAET BRAUNSCHWEIG, GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE NAMES OF FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V. AND TECHNISHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0277. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO THREE ORGANIZATIONS;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023351/0807 Owner name: CHARITE-UNIVERSITATSMEDIZIN BERLIN, GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE NAMES OF FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V. AND TECHNISHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0277. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO THREE ORGANIZATIONS;ASSIGNORS:MULLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023351/0807 |
|
AS | Assignment |
Owner name: TECHNISCHE UNIVERSITAET BRAUNSCHWEIG,GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE SPELLING OF THE ASSIGNEE'S NAME FROM TECHNISCHE UNIVERSITAT BRAUNSCHWEIG TO TECHNISCHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0282. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO TECHNISCHE UNIVERSITAET BRAUNSCHWEIG;ASSIGNOR:SCHILLING, MEINHARD;REEL/FRAME:023657/0830 Effective date: 20071122 Owner name: TECHNISCHE UNIVERSITAET BRAUNSCHWEIG, GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE SPELLING OF THE ASSIGNEE'S NAME FROM TECHNISCHE UNIVERSITAT BRAUNSCHWEIG TO TECHNISCHE UNIVERSITAET BRAUNSCHWEIG PREVIOUSLY RECORDED ON REEL 020281 FRAME 0282. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO TECHNISCHE UNIVERSITAET BRAUNSCHWEIG;ASSIGNOR:SCHILLING, MEINHARD;REEL/FRAME:023657/0830 Effective date: 20071122 Owner name: FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWAN Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE FIRST ASSIGNOR FROM MULLER TO MUELLER; REMOVE TECHNISHE UNIVERSITAET BRAUNSCHWEIG & CHARITE-UNIVERSITATSMEDIZIN BERLIN ASSIGNEES PREVIOUSLY RECORDED ON REEL 023351 FRAME 0807. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT TO FRAUNHOFER-GESELLSCHAFT ZUR FOERDERUNG DER ANGEWANDTEN FORSCHUNG E.V.;ASSIGNORS:MUELLER, KLAUS-ROBERT;BLANKERTZ, BENJAMIN;CURIO, GABRIEL;SIGNING DATES FROM 20071022 TO 20071031;REEL/FRAME:023657/0823 |
|
AS | Assignment |
Owner name: LEICA GEOSYSTEMS PTY LTD, AUSTRALIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:DUSHA, DAMIEN;REEL/FRAME:027814/0312 Effective date: 20110127 |
|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
AS | Assignment |
Owner name: TECHNISCHE UNIVERSITAET BRAUNSCHWEIG, GERMANY Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE ASSIGNMENT FILED IN ERROR AND ULTIMATELY RE-RECORD TO REMOVE THE ASSIGNMENT PREVIOUSLY RECORDED ON REEL 027814 FRAME 0312. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT FILED ON 03/06/2012 WAS FILED IN ERROR AND IS TO BE REMOVED FROM APPLICATION NO. 11/722,495;ASSIGNOR:SCHILLING, MEINHARD;REEL/FRAME:028349/0708 Effective date: 20071122 |
|
CC | Certificate of correction | ||
FEPP | Fee payment procedure |
Free format text: PAYOR NUMBER ASSIGNED (ORIGINAL EVENT CODE: ASPN); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Free format text: PAYER NUMBER DE-ASSIGNED (ORIGINAL EVENT CODE: RMPN); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY |
|
FPAY | Fee payment |
Year of fee payment: 4 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 8TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1552); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 8 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 12TH YEAR, LARGE ENTITY (ORIGINAL EVENT CODE: M1553); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY Year of fee payment: 12 |